Steerable and controllable medical laser fibers

ABSTRACT

A device includes a catheter section comprising a flexible joint region disposed between a distal end and a proximal end. The device includes a laser fiber disposed within the catheter section. The laser fiber emits laser light at a fiber distal end. The device includes a wire comprising a distal end coupled to the catheter section. The wire is configured to move the distal end of the catheter section from a first position to a second position about the flexible joint region.

RELATED APPLICATION

This application claims the benefit of U.S. Patent Application No.61/600,981, filed Feb. 20, 2012.

This application is a continuation in part application of U.S. patentapplication Ser. No. 11/641,490, filed Dec. 19, 2006.

This application is a continuation in part application of U.S. patentapplication Ser. No. 11/703,997, filed Feb. 8, 2007.

This application is a continuation in part application of U.S. patentapplication Ser. No. 13/626,518, filed Sep. 25, 2012.

TECHNICAL FIELD

Embodiments described herein are generally in the field of intravasculardevices. More particularly, embodiments described herein relate tointravascular catheters having a flexible and manipulatable hinge orjoint region.

BACKGROUND

Lasers of various wavelengths coupled to laser fibers for the deliveryof laser energy are used in a number of medical procedures. Conventionallaser fibers however are not capable of being actuated or deflected togive the operator control of the distal tip of the laser fiber for priceplacement of the distal laser fiber tip.

INCORPORATION BY REFERENCE

All publications and patent applications mentioned in this specificationare herein incorporated by reference to the same extent as if eachindividual publication or patent application was specifically andindividually incorporated by reference.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a laser fiber catheter or housing, under an embodiment.

FIG. 2 is a laser fiber system comprising the pre-shaped laser fibercatheter including a lumen, and a laser fiber traversing at least aportion of the lumen, under an embodiment.

FIG. 3 is a laser fiber system comprising a steerable and controllablelaser fiber catheter including a lumen, and a laser fiber traversing atleast a portion of the lumen, under an alternative embodiment.

FIG. 4 shows deflection of a distal tip of the steerable andcontrollable laser fiber system, under an embodiment.

FIG. 5 is a table presenting select parameters of modern flexibleureteroscopes.

FIG. 6A shows an external view of one variation of the catheterassembly, under an embodiment.

FIGS. 6B and 6C show alternative configurations of the distal region ofthe catheter assembly, under an embodiment.

FIG. 7A shows a cross sectional view of a proximally placed hinge regionin a variation of the distal region of the catheter assembly, under anembodiment.

FIG. 7B shows a cross sectional view of a mid-balloon hinge regionplacement for another variation of the distal region of the catheterassembly, under an embodiment.

FIG. 7C shows a cross sectional view of a distally placed hinge regionin another variation of the distal region of the catheter assembly,under an embodiment.

FIG. 7D shows a cross sectional view of an additional mid-balloon hingeregion placement for another variation of the distal region of thecatheter assembly, under an embodiment.

FIGS. 8A-8H show cross-sectional views of catheter shafts displaying thevarious relative positions of the push-pull wire lumen, main lumen, andoptional inflation lumen, under an embodiment.

FIG. 9A shows a cross-sectional side view of another variation of acatheter assembly, under an embodiment.

FIG. 9B shows a detail side view in which a portion of the tubingdefining the main lumen extends as an extension past a distal face ofthe joint region, under an embodiment.

FIG. 9C shows an end view of the flexible joint region, under anembodiment.

FIG. 9D shows a cross-sectional end view of the catheter bodyillustrating the wire lumen and the main lumen, under an embodiment.

FIG. 10A shows an assembly side view of the distal portion of avariation of the catheter assembly, under an embodiment.

FIGS. 10B and 10C show bending of the flexible joint regions ofcatheters having differing lengths of the flexible joint regions, underan embodiment.

FIGS. 11A and 11B show cross-sectional side and detail side views,respectively, of another variation of the device where the distal endmay be fused down by a liner, under an embodiment.

FIGS. 12A to 12C show side, end, and partially removed side views,respectively, of one variation of a control handle for manipulating thepush-pull wire, under an embodiment.

FIGS. 12D and 12E show detail views of the wheel and rack, respectively,used to manipulate the push-pull wire, under an embodiment.

FIG. 13 shows another variation in the cross-sectional side view ofcombination fitting/handle assembly, under an embodiment.

FIG. 14 shows another variation in the cross-sectional side view of thehandle body utilizing a carriage screw, under an embodiment.

FIG. 15 shows another variation in the cross-sectional side view of thehandle body utilizing a control/release knob, under an embodiment.

FIG. 16 shows another variation in the cross-sectional side view of thehandle body utilizing a control slide, under an embodiment.

FIG. 17 is a cross-sectional view of another variation of the distalregion of the catheter assembly including a coil over a distal portionof the push-pull wire, under an embodiment.

FIG. 18 is a perspective diagrammatic view illustrating the variation ofthe distal region of the catheter assembly including a coil over adistal portion of the push-pull wire, under an embodiment.

FIG. 19 is a cross-sectional view of another variation of the distalregion of the catheter assembly including a strapping coil over a distalportion of the catheter body, under an embodiment.

FIG. 20 is a cross-sectional view of another variation of the distalregion of the catheter assembly including a mesh over a distal portionof the catheter body, under an embodiment.

FIG. 21 is a perspective diagrammatic view showing the variation of thedistal region of the catheter assembly including a mesh over a distalportion of the catheter body, under an embodiment.

DETAILED DESCRIPTION

Embodiments are described herein comprising lasers of variouswavelengths coupled to laser fibers for the delivery of laser energy foruse in a number of medical procedures. Embodiments described hereincomprise a device including a catheter section having a flexible jointregion disposed between a distal end and a proximal end. The deviceincludes a laser fiber disposed within the catheter section. The laserfiber emits laser light at a fiber distal end. The device includes awire comprising a distal end coupled to the catheter section. The wireis configured to move the distal end of the catheter section from afirst position to a second position about the flexible joint region.

In urology, for example, the introduction of lasers and flexibleendoscopes has broadened the urological armamentarium for the treatmentof various urological conditions. Laser lithotripsy, first usedclinically in the late 1980s, uses laser light energy delivered througha quartz laser fiber, directed endoscopically through a working channelof the flexible or rigid endoscope and onto a calculus (stone). Amechanism of action surrounding laser lithotripsy of urological stonesoccurs via plasma formation between the distal laser fiber tip and thestone, which develops an acoustic shockwave, disrupting the stone alongfracture lines. Small quartz fibers, for example 200 and 325 micron corediameter quartz laser fibers, coupled to lasers such as a holmium laser,are passed easily through working channels of ureteroscopes (flexible orrigid endoscopes designed to enter the ureter through the urethra andbladder), fragmenting most stone compositions. The flexibleureteroscope, having distal actuation by operator proximal control, mayhelp the physician generally align the small quartz laser fiber. Manytimes intraoperatively, additional control for improved placement of thedistal laser fiber tip is desired. However, the conventional art as wellas commercially available quartz laser fibers do not have a mechanism ormechanisms that allows for proximal control of the distal tip of thelaser fiber for precise control and placement against the stone ortissue.

Urologists often use endoscopes in diagnosing and treatment pathologyalong the urinary tract (kidney, ureter, bladder, urethra). For example,in the case of the ureter (muscular cylindrical conduit, 25 to 30 cm inlength, connecting the kidney to the bladder that allows urine to flowfrom the kidney to the bladder via the ureter), rigid ureteroscopesconsist of a long thin tube with channels for irrigation (both inflowand outflow), means to pass a device (working channel), optical systemto view the ureter, and light fiber bundle to illuminate the viewingfield. The working channel generally has an internal diameter (ID) onthe order of 5 French (Fr; 3 Fr=1 mm). The outside diameter (OD) of arigid ureteroscope generally ranges from 6 Fr to 9 Fr, and is taperedfrom the proximal to the distal such that the distal tip has thesmallest OD when compared to the proximal. Alternatively, flexibleureteroscopes are flexible along the entire working length and, inparticular, have an internal actuation mechanism for in-plane deflectionof the distal tip on the order of 270°. Generally, flexible ureterscopeshave an OD ranging from 8 to 10 Fr and a working channel ID ofapproximately 3.6 Fr, allowing the use of instruments up to 3 Fr whilestill permitting adequate irrigation.

The basic components of flexible ureteroscopes include the opticalsystem, deflection mechanism for the distal tip, and working channel.The optical system consists of flexible fiberoptic image andillumination light bundles. Small lenses attached to the proximal anddistal ends of the image bundle create a telescope with imagemagnification, increased field of view, and focusing ability.Improvements in image bundle construction have allowed closer packing ofmore fibers, resulting in improved images, smaller outer diameters, andlarger working channels in both rigid and flexible ureteroscopes.Another design modification of the light bundle is the splitting of thisbundle distally into more than one point of light transmission. Thispermits a more centrally placed working channel as well as betterdistribution of the light within the working field. FIG. 5 is a tablepresenting select parameters of conventional flexible ureteroscopes.

The deflection mechanism of flexible ureteroscopes permitsmaneuverability within the urinary tract system. Most deflectingmechanisms consist of control wires running along the length of theureteroscope and are attached on the proximal end to a manually operatedlever mechanism. The wires traverse along the length of the ureterscopean distally the wires run through moveable metal rings to the distal tipwhere they are fixed. Moving a proximal lever up or down will pull thecontrol wire and move the tip. When the tip moves in the same directionas the lever, the deflection is “intuitive” (i.e., moving the proximallever down deflects the distal tip down and moving the proximal level upmoves the distal up). Modern flexible ureteroscopes allow both up anddown deflection in a single plane. This plane of deflection is marked bythe reticle seen as a notch within the field of view of theureteroscope. Modern flexible ureteroscopes permit down deflection ofapproximately 180°.

A study investigating the angle between the major axis of the ureter andthe lower pole infundibula (ureteroinfundibular angle) reported theaverage angle to be 140° with a maximum of 175°. Active deflection ofthe ureteroscope of 180° is necessary to allow visualization of thelower pole in most patients. However, reaching into the lower pole calyxwith the tip of the ureteroscope can be difficult.

The flexible ureteroscopes have a more flexible segment or joint of theureteroscope due to a material and/or structural changes of the sheathsuch as durometer, located just proximal to the point of activedeflection (joint). The ability to engage the passive secondarydeflection depends upon the ability to passively bend this portion ofthe ureteroscope off of the superior portion of the renal pelvis forexample. This can be difficult or impossible in patients withsignificant hydronephrosis. Additionally, once the tip of theureteroscope has been extended into the lower pole calyx, the ability tomanipulate working instruments and work within the calyx, using activeprimary deflection, can be challenging.

Conventional deflecting mechanism technology attempted to overcome thisdeficiency. The DUR-8 Elite (Gyms ACMI, Stamford, Conn., USA) is aflexible ureteroscope that incorporates active secondary deflection. Inaddition to the active primary deflection (185° down, 175° up) thesecondary deflection is now active, 165° down. It is controlled with anadditional lever opposite the existing primary deflection lever and canbe locked in place. Secondary deflection is not dependent upon passivemanipulation of the scope off of the upper portion of the renal pelvis.The degree of secondary deflection is not dependent upon the position ofthe scope or resistance to advance the scope but is controlled with thedeflecting lever. Severe hydronephrosis will not prevent the use ofsecondary deflection. Locking the secondary deflection in place cansimplify manipulation of the primary deflection within the lower polecalyx. The usefulness of this active secondary deflection of the DUR-8Elite was evaluated and it was found that the dual deflecting DUR-8Elite ureteroscope was helpful in cases in which the single deflectionflexible instruments fail to access and treat upper urinary tractpathology.

Karl Storz Endoscopy (Tuttlingen, Germany) has introduced “exaggerateddeflection” with their Flex-X model flexible ureteroscope. Thismodification of the deflection mechanism permits active primarydeflection to 300°. When approaching the lower pole calyx, the tip willextend out as it is deflected against the lower pole infundibulum.

Ureteral stones that cannot be extracted in total are candidates forfragmentation via ureteroscopic lithotripsy including electromechanicallithotripsy (e.g. Lithoclast, Boston Scientific), electrohydrauliclithotripsy (EHL), and laser lithotripsy (holmium laser lithotripsy).Laser lithotripsy has the advantage of minimizing trauma to the ureterand reducing stone dislocation. The holmium laser has dramaticallyimproved intraluminal lithotripsy and has become the intraluminallithotripsy energy of choice for most urologists. The holmium laser hasa wavelength of 2,100 nm, which is absorbed in 3 mm of water and 0.4 mmof tissue, making it very safe for use in urology. Fragmentation of thestone occurs via a photothermal reaction within the crystalline matrixof stone. By not relying upon shock-wave generation for stonefragmentation, the photothermal reaction produces stone dust rather thanfragments, effectively removing a moderate volume of the stone. Smallquartz laser fibers can be used with both rigid and flexibleureteroscopes to deliver laser energy from the holmium laser to thestone. Quartz laser fibers are available in various sizes. The mostcommon fibers used range from core sizes of 200 microns to 325 microns.None of the currently available laser fibers, however, have a mechanismor mechanisms that allows for proximal control of the distal tip of thefiber to steer, manipulate, and/or control the deflection or actuationof the distal tip for precise placement against the stone.

Benign prostatic hyperplasia (BPH) is the most prevalent disease entityin elderly men. In the late 1980s, lasers became a novel way to open awider channel and improve voiding dynamics. Many different techniquesunder the term laser prostatectomy have evolved. Individual techniquesmay vary greatly, but the two main tissue effects include coagulationand vaporization. Coagulation occurs when somewhat diffusely focusedlaser energy heats tissue and temperatures reach as high as 100° C.Proteins denature and necrosis ensues, resulting in subsequent sloughingof necrotic tissue (i.e., a debulking of the prostate). This process maytake as long as several weeks to complete and often initially results inedema, which transiently increases prostate volume (and therefore mayrequire short-term urethral catheterization).

The principle representative procedures in the laser coagulationcategory include visual laser ablation of the prostate (VLAP) usingNd:YAG and interstitial laser coagulation (ILC). VLAP uses a directtransurethral viewing source (cystoscope and coupled to a video camera)along with a laser that is supplemented by a visible (usuallyhelium-neon) aiming beam. Interstitial coagulation using a diode laseris another coagulative technique in which optical fibers are introducedtransurethrally or perineally directly into the prostate. This can causelarge-volume necrosis with atrophy while preserving the urethral mucosa.

In several studies these coagulative procedures have proven to haveunacceptably high adverse events, namely irritative voiding, dysuria,and other storage symptoms, as well as high reoperation rates.Additionally, more efficient and improved laser applications such asHo:LEP and photo-vaporization (PVP) techniques have shown to be moreeffective largely replacing VLAP and ILC. Vaporization occurs whengreater laser energy is focused (increased power density) and tissuetemperatures reach as high as 300° C. This causes tissue water tovaporize and results in an instantaneous debulking of prostatic tissue.The high-power (80-W) potassium-titanyl phosphate laser (KTP orGreenlight) is commonly used for its vaporization effects on prostatetissue. This procedure is associated with significantly less bleedingand fluid absorption than standard transurethral prostate resection.Because of this, the KTP laser is safely used in seriously ill patientsor those receiving oral anticoagulants. Additionally, the KTP laser'sease of use has made it an attractive option for urologists. Drawbacksto the KTP procedure compared with traditional TURP include the lack oftissue obtained for postoperative pathological analysis and theinability to diagnose and unroof concomitant prostatic abscesses.

A higher-powered 120-W LBO laser (GreenLight HPS) was developed and evenmore recently the 180-W LBO system (GreenLight XPS) has been marketed toimprove upon current vaporization speed. Whether these newer generationKTP lasers are clinically superior to their predecessor remains to beseen.

Laser energy has been used to incise or enucleate prostate adenomas downto the capsule, making this procedure the endoscopic analog of opensimple prostatectomy. The Ho:YAG is ideally suited for this task becauseit creates precise incisions, cuts by vaporizing tissue with adequatehemostasis, and leaves minimal collateral damage. Advantages of thismethod include the availability of a specimen for histologicexamination, less postoperative catheter time, and the ability to exciselarge adenomas. Drawbacks include greater training time and the need totransport the adenoma (in toto or portioned) into the bladder tomorcellate it prior to removal.

For some time, the criterion standard treatment for BPH has been TURPand the standard by which all of the above techniques are compared. TURPis used less frequently because of associated complications, includingbleeding and transurethral resection (TUR) syndrome and the improvedefficacy of medical therapies. Additionally, the preponderance ofurology patients taking chronic oral anticoagulants and anti-platelettherapy mandate the need for techniques that can be safely performed inthis setting. In general, the laser prostatectomies mentioned above haveadded safety and less perioperative pain compared with TURP. Lessbleeding occurs and the operative time is usually less; therefore, mosttypes may be performed on patients who are receiving anticoagulants.

Laser modalities are safer than TURP in the perioperative period,although some may have a similar long-term complication profile. Thecoagulative approaches have been largely abandoned because ofpost-operative symptomatology and the availability of other modalities.Vaporization techniques, particularly Greenlight PVP, have achievedwidespread popularity, largely because of their ease of use and theability to perform these procedures on an outpatient basis. HoLAP isalso a viable vaporization technique and in fact a RCT showedessentially equivalent efficacy and complication rates when comparedwith Greenlight PVP. Only operative time favored PVP. HoLAP requires themost technical expertise with a correspondingly steep learning curve butis likely the optimal endoscopic approach to the very large gland.Although all of the modalities mentioned are efficacious, none isefficacious enough to make the old-fashioned TURP obsolete.

In all of the aforementioned laser procedures for the treatment of BPH,none of the laser fibers used in these procedures can be actuated ordeflected to give the operator control of the distal tip of the laserfiber for price placement of the distal laser fiber tip.

Various laser energies have been used to treat bladder and upper urinarytract urothelial tumors. Most commonly, holmium and Nd:YAG are used inthis setting. Quartz laser fibers are directed endoscopically to deliverlaser energy to the tissue. The Nd:YAG laser energy is used to coagulateand ablate with a thermal effect that extends deeper than other lasers.Holmium is more precise, with less of a coagulative effect. Theadvantages of laser therapy for tumor ablation include less bleedingand, as such, catheter drainage is usually unnecessary. A lowerincidence of stricture formation results when compared withelectrocautery because fibrotic reaction is minimal. The laser techniquedecreases the need for anesthesia, causes less postoperative pain, andallows a quicker return to work. The Ho:YAG laser can be used through aflexible cystoscope to ablate recurrent superficial bladder tumors in anoffice setting. A recent review of patients treated with the flexiblecystoscope reported a high degree of satisfaction because this methodavoided the need for general anesthesia and reduced post-operative pain.No pathology specimen is available, thus, determining depth of invasionis impossible unless multiple prior biopsy samples were obtained.Another drawback, especially with the Nd:YAG laser, is that the area ofdestruction is deep and not fully visualized. Some reports of bowelperforation exist when treating bladder dome lesions even withoutvisible bladder perforation secondary to the effect of Nd:YAG. In thissetting, Ho:YAG is a better choice. In all of the aforementioned laserprocedures for the treatment of urothelial malignancies, however, noneof the laser fibers used in these procedures can be actuated ordeflected to give the operator control of the distal tip of the laserfiber for price placement of the distal laser fiber tip.

Urethral strictures have been a frustrating entity for the urologist totreat. Many different procedures are available to deal with them, butall of them, except open urethral reconstruction, are associated with ahigh rate of recurrence. Internal urethrotomy yields a success rate ofonly 20-40%, and repeat procedures, unfortunately, offer littleimprovement. Nd:YAG, KTP, and Ho:YAG lasers have all been usedexperimentally to vaporize fibrous strictures. They can yield recurrencerates similar to those of the cold-knife internal urethrotomy. Recently,some hope of using an Nd:YAG laser with a crystal contact tip at the endof a delivery fiber has occurred. In a study of 42 patients withurethral strictures, the Nd:YAG crystal tip contact method ofvaporization yielded a 93% success rate that was durable for a mean ofover 2 years. However, in all of the aforementioned laser procedures forthe treatment of urothelial stricture disease, none of the laser fibersused in these procedures can be actuated or deflected to give theoperator control of the distal tip of the laser fiber for priceplacement of the distal laser fiber tip.

Similarly, in other rigid scope procedures such as arthroscopy of theknee or endoscopic procedures of the abdomen, the availability of adeflectable or actuated laser fiber would improve these and otherendoscopic surgical procedures by offering the physician laser distaltip control to accurately and/or efficiently place the fiber in adesired position or location for laser treatment.

While preferred embodiments of the present invention are shown anddescribed herein, it will be obvious to those skilled in the art thatsuch embodiments are provided by way of example only. Numerousvariations, changes, and substitutions will now occur to those skilledin the art without departing from the invention. It should be understoodthat various alternatives to the embodiments of the invention describedherein may be employed in practicing the invention.

FIG. 1 is a laser fiber catheter or housing, under an embodiment. Thelaser fiber catheter comprises a pre-shaped laser fiber catheter, but isnot so limited. FIG. 2 is a laser fiber system or assembly comprisingthe pre-shaped laser fiber catheter including a lumen, and a laser fibertraversing at least a portion of the lumen, under an embodiment. In thisembodiment, the laser fiber system comprises a first component that isthe deflectable and controllable catheter or housing, and a secondcomponent that is a laser fiber. The laser fiber is reversibly placedinto at least a portion or segment of the lumen of the deflectable andcontrollable laser fiber catheter, but is not so limited.

The pre-shaped laser fiber catheter of the laser fiber system comprisesa single lumen catheter or tube fabricated from materials that includeone or more of thermoplastic polymers or polymer blends (e.g.,polyurethane and polyamide, etc.), with a luer or hub and strain reliefcomponent positioned at a proximal end or region of the catheter. Thepre-shaped laser fiber catheters are available in various lengths where,in an embodiment, the lengths are in a range of approximately 0.25meters (m) to 3.0 meters. The laser fiber catheters accept laser fibersof various diameters, for example, a diameter of approximately 160microns. The thermoplastic polymer catheters of an embodiment arepre-shaped to form one or more distal tip shapes, for examplesemi-circular distal tip configuration, and semi-oval distal tipconfiguration to name a few. The physician or operator of the laserfiber system can also shape the distal tip of the catheter to a shapeappropriate to one or more of a procedure in which the system is to beused and a region of a biological entity in which the system is to beused.

The laser fiber is inserted through the hub on the proximal end of thecatheter and pushed through a length of the pre-shaped catheter untilthe distal end of the laser fiber emerges from the distal end of thecatheter. The hub of an embodiment includes a clutch or brake mechanismsuch that once the laser fiber is positioned within and through thecatheter at the desired position, the clutch or brake mechanism isactuated, engaging and fixing the desired position of the laser fiber.The combination of the pre-shaped catheter and the laser fiber isreferred to as the laser fiber system but is not so limited.

An example of an operational scenario involving use of the laser fibersystem includes laser lithotropsy of a ureteral stone. In thisprocedure, the laser fiber system is placed into the working channel ofthe flexible or rigid ureteroscope via the working channel port. As thelaser is pushed distally into working channel, it emerges from thedistal end of the ureteroscope such that it is positioned adjacent tothe ureteral stone. For a given fixed position of the ureteroscope, thelaser fiber system can be accurately placed in the surgical field ofview by pushing or pulling the laser fiber system and, if needed,torquing the laser fiber system, as described in detail herein.

An alternative embodiment of the laser fiber device herein includes alaser fiber endoscope or housing. The endoscope of this embodiment is amedical device comprising a long, thin, flexible (or rigid) tube thatincludes a light and a video camera. More particularly, the endoscope ofan embodiment comprises a rigid or flexible tube, a light deliverysystem to illuminate the organ or object under inspection, a lens systemtransmitting the image from the objective lens to the viewer (e.g., arelay lens system in rigid endoscopes, or a bundle of optical fibers ina fiberscope), an eyepiece, and an additional lumen or channel to allowentry of medical instruments or manipulators. The lumen of the endoscopehouses at least one laser fiber. The laser fiber is inserted through anopening or channel at the proximal end of the endoscope and pushedthrough a length of the endoscope until the distal end of the laserfiber emerges from the distal end of the endoscope. In this embodiment,the combination of the endoscope and the laser fiber is referred to asthe laser fiber system but is not so limited. The laser fiber endoscopedescribed herein can be used in any field of endoscopy, including butnot limited to endoscopy of the gastrointestinal tract (GI tract) (e.g.,oesophagus, stomach and duodenum (esophagogastroduodenoscopy), smallintestine (enteroscopy), large intestine/colon (colonoscopy,sigmoidoscopy), magnification endoscopy, bile duct (endoscopicretrograde cholangiopancreatography (ERCP), duodenoscope-assistedcholangiopancreatoscopy, intraoperative cholangioscopy), rectum(rectoscopy) and anus (anoscopy) (collectively referred to asproctoscopy)), respiratory tract (e.g., nose (rhinoscopy), lowerrespiratory tract (bronchoscopy)), ear (e.g., otoscope), urinary tract(e.g., cystoscopy), female reproductive system (gynoscopy) (e.g., cervix(colposcopy), uterus (hysteroscopy), fallopian tubes (falloposcopy)),normally closed body cavities (e.g., using a small incision) (e.g.,abdominal or pelvic cavity (laparoscopy), interior of a joint(arthroscopy), organs of the chest (thoracoscopy and mediastinoscopy)),during pregnancy (e.g., amnion (amnioscopy), fetus (fetoscopy)), plasticsurgery, panendoscopy (triple endoscopy, combines laryngoscopy,esophagoscopy, and bronchoscopy), orthopedic surgery (e.g., handsurgery, such as endoscopic carpal tunnel release, epidural space(epiduroscopy), bursae (bursectomy)), endodontic surgery (e.g.,maxillary sinus surgery, apicoectomy), and non-medical uses forendoscopy (e.g., pre-visualization of scale models (architecturalendoscopy), internal inspection of complex technical systems(borescope), examination of improvised explosive devices by bombdisposal personnel, surveillance via tight spaces).

The laser fiber catheter comprises a pre-shaped laser fiber catheter,but is not so limited. FIG. 2 is a laser fiber system or assemblycomprising the pre-shaped laser fiber catheter including a lumen, and alaser fiber traversing at least a portion of the lumen, under anembodiment. In this embodiment, the laser fiber system comprises a firstcomponent that is the deflectable and controllable catheter or housing,and a second component that is a laser fiber. The laser fiber isreversibly placed into at least a portion or segment of the lumen of thedeflectable and controllable laser fiber catheter, but is not solimited.

The pre-shaped laser fiber catheter of the laser fiber system comprisesa single lumen catheter or tube fabricated from materials that includeone or more of thermoplastic polymers or polymer blends (e.g.,polyurethane and polyamide, etc.), with a luer or hub and strain reliefcomponent positioned at a proximal end or region of the catheter. Thepre-shaped laser fiber catheters are available in various lengths where,in an embodiment, the lengths are in a range of approximately 0.25meters (m) to 3.0 meters. The laser fiber catheters accept laser fibersof various diameters, for example, a diameter of approximately 160microns. The thermoplastic polymer catheters of an embodiment arepre-shaped to form one or more distal tip shapes, for examplesemi-circular distal tip configuration, and semi-oval distal tipconfiguration to name a few. The physician or operator of the laserfiber system can also shape the distal tip of the catheter to a shapeappropriate to one or more of a procedure in which the system is to beused and a region of a biological entity in which the system is to beused.

The laser fiber is inserted through the hub on the proximal end of thecatheter and pushed through a length of the pre-shaped catheter untilthe distal end of the laser fiber emerges from the distal end of thecatheter. The hub of an embodiment includes a clutch or brake mechanismsuch that once the laser fiber is positioned within and through thecatheter at the desired position, the clutch or brake mechanism isactuated, engaging and fixing the desired position of the laser fiber.The combination of the pre-shaped catheter and the laser fiber isreferred to as the laser fiber system but is not so limited.

An example of an operational scenario involving use of the laser fibersystem includes laser lithotropsy of a ureteral stone. In thisprocedure, the laser fiber system is placed into the working channel ofthe flexible or rigid ureteroscope via the working channel port. As thelaser is pushed distally into working channel, it emerges from thedistal end of the ureteroscope such that it is positioned adjacent tothe ureteral stone. For a given fixed position of the ureteroscope, thelaser fiber system can be accurately placed in the surgical field ofview by pushing or pulling the laser fiber system and, if needed,torquing the laser fiber system, as described in detail herein.

FIG. 3 is a laser fiber system comprising a steerable and controllablelaser fiber catheter including a lumen, and a laser fiber traversing atleast a portion of the lumen, under an alternative embodiment. In thisembodiment, the laser fiber system comprises a first component that isthe steerable and controllable catheter or housing, and a secondcomponent that is the laser fiber. The laser fiber is reversibly placedinto at least a portion or segment of the lumen of the steerable andcontrollable laser fiber catheter, but is not so limited. FIG. 4 showsdeflection of a distal tip of the steerable and controllable laser fibersystem, under an embodiment.

The steerable and controllable catheter of the laser fiber systemcomprises a flexible joint region that defines a main lumen and at leastone wire lumen. The flexible joint region is located at a distal end orregion of the steerable and controllable catheter assembly and isconfigured to be more flexible when compared to the assembly proximal tothe joint. The flexible joint region has a predetermined lengthconfigured or sized to affect or control a flexure (e.g., reducedstiffness) of the flexible joint region. The wire lumen, in anembodiment, is positioned adjacent to the main lumen, but is not solimited. The main lumen houses the laser fiber but is not so limited.The wire lumen defines an opening at or near a distal region or end ofthe flexible joint region. The laser fiber system includes a push-pullwire positioned in at least a portion of the wire lumen and configuredto be pushed or pulled along a longitudinal axis of the wire lumen.

The wire lumen of an embodiment comprises a braided or non-braidedlumen, as described in detail herein. When the braided lumen is used,the braid may traverse a portion or segment of the lumen or an entirelength of the lumen. Furthermore, the braid configuration of anembodiment may be constant and uniform or, alternatively, comprise avaried braid pitch resulting in changes in stiffness. The braid may bemade from a number of materials, for example, super-elastic alloys, butis not so limited.

The deflection or movement of the flexible joint is controlled in anembodiment by a push-pull wire such that it deflects when the push-pullwire is moved or manipulated at the proximal aspect of the catheterassembly. The flexible joint may be varied to extend beyond the braidtermination, or it may be extended to the deflecting portion toencompass a portion of the braid. By varying the length of the flexiblejoint region, the radius or amount of curvature or joint flexure regioncan be controlled. For example, a joint region having a relativelyshortened length between the distal end of the joint region and theterminal end of the braid allows for reduced flexion relative to aneutral position of the steerable and controllable laser fiber assembly.A lengthened joint region extending to a more proximally locatedterminal end facilitates more flexion when compared to a shorter jointregion. As such, flexure may be controlled in part by the length of theflexible joint region. To further facilitate flexion of the laser fiberassembly and control of bending, additional members such as coils may beincorporated into the transition region of the laser fiber systemassembly.

The laser fiber system of an alternative embodiment includes a wireattachment band at or near the distal end or region of the flexiblejoint region. The wire attachment band secures the push-pull wire to thedistal end or region. Again, the flexible joint region has apredetermined length configured or sized to affect or control a flexure(e.g., reduced stiffness) of the flexible joint region.

The laser fiber system of another alternative embodiment comprises twoor more longitudinal lumens, but is not so limited. The two lumensinclude a first lumen running the length of the assembly and housing thelaser fiber, and a second lumen running at least a portion of the lengthof the assembly and housing the push-pull wire. The steerable andcontrollable laser fiber assembly can have a consistent and constantcross section throughout its length or, alternatively, the cross sectionmay vary from proximal to distal end. Furthermore, the materialproperties of the polymer of the steerable and controllable laser fiberassembly may vary along the length so as to vary the column stiffness.For example, the proximal third of the laser fiber assembly may bestiffer when compared to the middle third of the laser fiber assembly,but the embodiment is not so limited.

The fiber catheter or housing of the embodiments described abovecomprises a catheter or catheter section that includes a main lumen, awire lumen housing a push-pull wire, and a flexible joint region. Thecatheter section includes a control including a handle and a wirecontrol member engaging the push-pull wire for manipulating the flexiblejoint region. The push-pull wire may be tapered, having a proximalportion of a first diameter and a smaller diameter distal portion. Acoil may be placed around the smaller diameter to prevent buckling ofthe smaller diameter portion. A strapping coil may also disposed aroundthe outside of the catheter, and an outer covering may be disposedaround the strapping coil. An outer covering of a mesh may also bedisposed around the distal tip of the catheter. Descriptions of thecatheter or catheter section of an embodiment follow.

The catheter of an embodiment involves a multi-lumen catheter. Thedevice may optionally include a balloon member. The catheter includes ashapeable, flexible distal section which may be in the vicinity of theballoon, if the balloon member is utilized. The flexible section, or“hinge region”, is manipulated from outside the body during the processof delivering the vaso-occlusive device or material. The terms “hingeregion”, “hinge”, or “flexible joint” may be used interchangeably.

FIG. 6A shows a catheter assembly 23, under an embodiment. Thisvariation of the catheter assembly 23 includes a catheter shaft 25comprising a flexible, thin walled body or tube 26 having an inner lumenwhich extends between proximal and distal catheter ends 24, 37,respectively. The tube 26 generally comprises a nondistensible polymerhaving the appropriate mechanical properties for this application, forexample polyethylene (e.g., HDPE, LDPE, LLDPE, MDPE, etc.), polyesters(such as Nylon), polypropylene, polyimide, polyvinyl chloride,ethylvinylacetate, polyethylene terephthalate (PET), polyurethane (e.g.,TEXIN such as that made by Bayer Corporation), PEBAX, fluoropolymers,such as polytetrafluoroethylene (PTFE), for example, mixtures of theaforementioned polymers, and their block or random co-polymers.

The catheter assembly can be used for access through the vasculature tothe brain often, but not necessarily, using a guide wire. If an optionalballoon member is included in the catheter assembly, the balloon membermay be inflated to close or to restrict any hollow body lumen, such asan artery, vein, orifice, cavity, etc., or the mouth of an aneurysmprior to or during placement of a vaso-occlusive device. Generally, theassembly may be flexed at a “hinge region” near or at the distal end ofthe catheter by a push-pull wire extending proximally through thecatheter. A main lumen defined through the catheter assembly can be usedfor the introduction of a vaso-occlusive device or material for eventualplacement in the vasculature.

The proximal catheter end 24 of an embodiment includes a fitting 18(e.g., a “LuerLok”) through which fluid may be supplied to thecatheter's inflation lumen through a side port 16. The proximal end ofthe catheter is provided with a second port 20 and a fitting 22 throughwhich the push-pull wire is used to manipulate the hinge region 32 inthe distal catheter tip. The proximal end fitting 18 includes an axiallyextending port 14 which communicates with the delivery/guide wire lumenof the catheter. The optional guide wire 12 may have any suitableconstruction for guiding the flexible catheter to its intended sitewithin the body. The proximal end of the guidewire 12 of an embodimentincludes a handle 10 for applying torque to the guidewire 12 duringcatheter operation, as described in further detail herein. The guidewiremay have a variable stiffness or stepped diameter along its length, forexample, a larger-diameter, stiffer proximal region and one or moresmaller-diameter, more flexible distal regions.

The distal portion 35 of the catheter may include an optional inflatablemember 30, for example a balloon. An opening 36 at the distal end of thecatheter may also be used for delivery of drugs and/or vaso-occlusivedevices to a pre-selected vascular site. The distal end region 35 of thecatheter 25 of an embodiment includes an inflatable balloon 30 which,when inflated, aids in the placement of vaso-occlusive materials ordevices by blocking the entrance to the aneurysm or the artery adjacentto the aneurysm.

Use of the balloon member is optional. When a balloon is used theballoon wall section (described in detail herein) is formed from a thinsleeve of polymeric material and attached at its opposite sleeve ends toa relatively more rigid tube section. FIGS. 6A, 6B, and 6C displayvarious configurations of the distal catheter tip 35 positioning basedon the placement of the flexible hinge region. FIGS. 6A, 6B, and 6C,respectively, show variations of the catheter 23 in which the hingeregion 32 is placed proximal to (FIG. 6A), within (FIG. 6B), and distalto (FIG. 6C) the inflatable member region 30 when such an inflatablemember 30 is included in the catheter assembly. Flexion of the hingeregion is achieved through remote manipulation of the push-pull wire 21,but is not so limited.

FIGS. 7A through 7D show variations of the distal end region 35 andhinge region 32 of the catheter described above with reference to FIGS.6A, 6B, and 6C. The catheter tube 40 of FIG. 7A may have an inflatablemember 44, e.g., a balloon, formed by an inflatable sleeve secured atits ends 41, 43 to the catheter tube wall 40. The inflatable member orballoon 44 may be of a shape, thickness, and material as is typical ofballoons used in neurovascular balloon catheters. The inflatable memberor balloon 44 may be formed of a thin polymeric material, and/or anelastomeric, stretchable material such as silicone rubber, latex rubber,polyvinyl chloride, complex co-polymers such as styrene-ethylenebutylene-styrene copolymers such as C-FLEX, or alternatively, anon-stretchable film material such as polyethylene, polypropylene, orpolyamides such as Nylon. Attachment of the sleeve ends to the cathetertube may be by adhesives, heat shrinkage, mechanical fasteners, or othersuitable method. Inflation lumen 42, which is also optional if balloon44 is included in the assembly, allows communication between theinflation fluid source and the balloon 44 through at least one opening50 formed in the catheter tube 40. Inflation and deflation of theballoon are effected by the passage of radio-opaque fluid, saline, orother fluid. A push-pull wire lumen 60 may extend throughout thecatheter tube 40 to protect the passage of the push-pull wire 62. Toassist in preventing collapse of the tube 60 enclosing the push-pullwire 62 and to prevent kinking or bulging during actuation, thepush-pull wire lumen 60 may have additional structure provided by alayer of higher stiffness polymer (e.g., a polyimide), a support coil,or a support braid, as described in detail herein.

Manipulation of the push-pull wire 62 via the proximal wire port 20 inFIG. 6A may result in flexion of the distal end 35 of the catheter 25.The guidewire 57 may extend through the delivery lumen 55 which liesinterior to the catheter tube 40. The push-pull wire 62 may extendthrough the push-pull wire lumen 60 and may be attached to radio-opaqueband 67, which may surround the catheter distal end 65 and may be madeof a variety of radio-opaque material such as stainless steel, platinum,gold, nickel, etc. The hinge region 58 at which the distal catheter tip65 flexes due to proximal manipulation of the push-pull wire 62 may belocated proximal to, within, or distal to the balloon (if used), asdisplayed respectively in FIGS. 7A, 7B, and 7C. Although the inclusionof a balloon with the catheter assembly is described herein, the balloonis optional and may be omitted entirely from the catheter assembly.

As shown in FIG. 7A, when the hinge region 58 is placed proximally ofthe balloon 44, the push-pull wire lumen 60 extends to a region which isproximal of the distal end of the balloon 44 to allow flexion of theregion of the catheter's distal end 65 which includes the entire balloon44. If the hinge region 58 is placed interior to the balloon, as in FIG.7B, flexion of the catheter's distal end 65 occurs such that the pointof flexion is within the balloon (also displayed in FIG. 6B). FIG. 7Cshows the placement of hinge 58 distal to the balloon; flexion duringdistal-hinge placement occurs such that the manipulatable region of thecatheter's distal end 65 does not include any portion of the balloon 44.

FIG. 7D shows placement of the hinge region 58 interior to the balloon44. The balloon 44 extends between the guidewire/delivery tube 56 andthe outer catheter tube 40 enclosing the annular inflation lumen 42. Thepush-pull wire 62 is attached to the distal end 65 of theguidewire/delivery lumen tube 56. In each of the variations shown inFIGS. 7A to 7D, the push-pull wire 62 may be attached at its distal endto the catheter through a variety of methods, for example, adhesives,crimping, and mechanical fasteners, to name a few. In this variation, aradio-opaque marker band 67 may be used to anchor the wire 62. Moreover,other attachment sites may be used for attachment of the push-pull wire62 distal to the hinge region 58. The push-pull wire itself is a wirewhich has sufficiently high column and tensile strengths such that itmay be pushed or pulled along a longitudinal axis of the wire throughthe wire lumen without buckling or kinking. It may be fabricated into awire having a circular cross-section, although other cross-sectionalshapes may be utilized, having a diameter, for instance, ranging from0.025 mm and higher. The push-pull wire may be fabricated from abiocompatible metallic material such as stainless steel, platinum, etc.Alternatively, the push-pull wire 62 may also include a tapered wirewhich has a larger diameter at or near its proximal end and a smallerdiameter at or near its distal end. Conventional guidewires may also beutilized as a push-pull wire, provided that it has an adequate diameterand sufficient column and tensile strengths desirable for manipulatingthe flexible distal end of the device.

In FIG. 7D, extension of the delivery lumen tube 56 beyond the end ofthe inflation lumen 42 allows remote manipulation of the catheter'sdistal end 65 if the push-pull wire 62 is attached to the catheterusing, e.g., markers or platinum bands 67. The delivery tube lumen 56may be made of any of the above materials with respect to tube 26 inFIG. 6.

Some of the various configurations of the catheter's lumina (e.g.,inflation, push-pull, delivery, etc.) are displayed in FIGS. 8A through811. In FIG. 8A, the optional inflation lumen 122 and push-pull wirelumen 124 are formed interior to the catheter wall 120, while theinterior catheter wall forms the guidewire lumen 128. In FIG. 8B, thecatheter wall 120 forms the guidewire lumen 128 that includes theoptional inflation lumen 122 and push-pull wire lumen 124. The optionalinflation lumen 122 is formed interior to the catheter wall 120 of FIG.8C, while the push-pull wire lumen 124 lies within the larger coil lumen128 (which is formed by the catheter wall 120).

FIG. 8D is a variation of FIG. 8C in which the push-pull wire lumen 124lies interior to the catheter wall 128 while the optional inflationlumen 122 lies within the larger main lumen 128. In FIG. 8E, theinterior catheter wall 120 forms the optional inflation lumen 122, andthe push-pull wire lumen 124 and the main lumen 128 are found within theinflation lumen 122. The optional inflation lumen 122 surrounds theguidewire lumen 128 and lies within the region formed interior catheterwall 120 in FIG. 8F, while the push-pull wire lumen 124 lies within thecatheter wall 120. In FIG. 8G, one shared lumen 123 serves as thepush-pull and optional inflation lumen; the shared push-pull andinflation lumen 123 along with the guidewire lumen 128 lie within thecatheter wall 120. Another alternate variation of the luminapositioning, shown in FIG. 811, has the push-pull wire lumen 124 lyinginterior to the inflation lumen 122 which is included within thecatheter wall 120, while a separate lumina for the guidewire 128 also isincluded within the catheter wall.

The tube constructions, hinge region construction, and other tubingforming the various lumina discussed herein may be created throughextrusion, sequential production (in which the parts are manufacturedseparately and later assembled together), or some other method.Moreover, if use of the balloon is omitted from the catheter assembly,the inflation lumen may be omitted entirely as well.

FIG. 9A shows a cross-sectional side view of another variation of acatheter assembly 210. This embodiment includes a catheter body 212 witha main lumen 216 defined through the length of the assembly 210. Thepush-pull wire lumen 214 may also be defined through the length of thecatheter body 212, or at least through a majority of the length ofcatheter body 212, extending from a fitting 232 at a proximal end of thecatheter assembly 210 to a region near or at the distal end of thedevice. The catheter body 212 may comprise several regions, each havinga different degree of flexibility. For instance, the catheter assembly210 may comprise a first portion 220 distal of the fitting 232 having afirst stiffness. A second portion 222, having a second stiffness andlocated distal of the first portion 220, may be more flexible relativeto the first portion 220. Likewise, a third portion 224, having a thirdstiffness and located distal of the second portion 222, may be moreflexible relative to the first and second portions 220, 222,respectively. Thus, the catheter body 212 may have a length comprisingprogressively more flexible sections that are farther distally locatedalong the catheter 212. Bending portion or flexible joint region 218 maybe positioned distal to the third section 224, as described in furtherdetail below.

The push-pull wire lumen 214 is reinforced along at least a substantialportion of its length. The wire lumen 214 may include a braided ribbon236 integrated throughout the length of lumen 214 along catheter bodylength 226. Alternatively, the braided ribbon 236 may be integratedthrough lumen 214 to terminate proximally of joint region 218, as shownin the FIG. 9A. The braided ribbon 236 may be a uniform braid or it maybe braided with a varying braid pitch. For instance, proximal sectionsof the catheter body 212, such as first portion 220, may have a braidwhich is tighter or which has a higher braid pitch than more distallylocated sections, such as third portion 224. When a region of lowerbraid pitch is flanked by regions of higher braid pitch, the region ofgreater pitch may generally be stiffer during manipulation of the distalcatheter tip.

The braided ribbon 236 may be made from a number of materials. Forinstance, the braided ribbon 236 of an embodiment includes metals whichare members of a class of alloys know as super-elastic alloys. Examplesuper-elastic alloys include the class of nickel-titanium materialstypically known as Nitinol. Other appropriate metals may also be used,such as stainless steel or polymers may also be used such as liquidcrystal polymers (LCPs). The braids of an embodiment are made usingcommercially available tubular braiders. The term “braid” may generallyinclude tubular constructions in which the ribbons making up theconstruction may be woven radially in an in-and-out fashion as theycross to form a tubular member defining a single lumen. Other braidingvariations may also be used. The braid may also be made from a suitablenumber of ribbons or wires. FIG. 9D shows a cross-section of catheterbody 212. As shown, wire lumen 214 may have a liner 246, e.g., alubricious polymeric liner, such as polytetrafluoroethylene (PTFE),available commercially under the trade name “TEFLON,” for example,disposed upon the lumen wall to facilitate movement of a push-pull wireof the lumen. The liner 246 may be made from any variety of suitablepolymeric materials as described herein. Alternatively, the braidedribbon 236 may be positioned upon the inner surface of wire lumen 214.In such a configuration, a lubricious coating may be optionally omittedfrom the distally located portions of the device.

Although three sections of variable stiffness are described inembodiments, this is intended to be illustrative. Catheters having asfew as two sections or multiple (e.g., more than two) sections ofvariable stiffness are also within the scope of the embodimentsdescribed herein. Furthermore, although the sections of an embodimenthave decreasing stiffness (or greater flexibility) distally along thecatheter body 212, other variations may include distally locatedsections with increasing stiffness or alternating sections of relativelystiffer and more flexible sections, or any other combinations.

First portion 220 may, for example in one variation, have a typicallength of about 100 centimeters (cm) (+/−1 cm) with a stiffness orrelative durometer hardness value of 72 D. The second portion 222 mayhave a length of about 30 cm (+/−1 cm) with a lower stiffness orhardness of 63 D. Third portion 224 may likewise have a length of about30 cm (+/−1 cm) with an even lower stiffness or hardness value of 40 D.In either case, the main lumen 216 may be defined by tubing having astiffness or relative hardness of, e.g., 63 D, encased throughout thelength of the device. Each of the sections is integral with adjacentsections. The variable stiffness may be effected through one of anyvariety of methods, e.g., different sheaths or coverings havingdiffering stiffness. For instance, PEBAX (Atochem Corporation of France)or any other polymeric material mentioned above, having the variablestiffness may be used to cover the respective sections.

The manipulatable or flexible joint region 218 is generally located atthe distal end of the catheter body 212 and is configured to bend whenmanipulated by the push-pull wire. Flexible joint region 218 may beconfigured to have a length ranging from, e.g., approximately 3 mm to 3cm. As described herein, the braided ribbon 236 may terminate proximallyof the flexible joint region 218. The bending portion 218 may be variedto extend to where braid 236 terminates, or it may be extended tobending portion 228 to encompass a portion of the braid 236. Theflexible joint region 218 may be covered by PEBAX, or any otherpolymeric material mentioned above, having a stiffness or hardness of,e.g., 25 D, which is lower than a stiffness of third portion 224.

As mentioned above, the proximal portion of the catheter body 212 of anembodiment is attached to fitting 232. Fitting 232 may be any variety offitting typically utilized with intra-luminal catheters. In thisvariation, fitting 232 may define an opening 234 which is incommunication with main lumen 216 to allow for the passage ofguidewires, various tools, therapeutic drugs, etc. It may also beconfigured to accept a separately manufactured push-pull wire handle 238with a control 240 for manipulating the push-pull wire distally orproximally along a longitudinal axis of the wire. Alternatively, thepush-pull wire handle 238 may be formed as an integrated piece withfitting 232. Although the figure shows the inclusion of opening 234 inthe proximal end of fitting 232, other variations may includerapid-exchange (RX) type catheter designs having guidewire lumenopenings defined along the body of catheter body 212.

The distal end of flexible joint region 218 may have a portion of thetubing defining the main lumen 216 extending as an extension 230 pastdistal face 242 of joint region 218, as shown in the detail side view ofFIG. 9B. The length of extension 230 may be configured to extend atvarious lengths from a relatively short length to a relatively longerlength, depending upon the desired bending results. Extension 230 mayhave a relative stiffness or hardness value, e.g., 63 D, which is higherthan the stiffness or hardness of the section located proximally, i.e.,flexible joint region 218. Moreover, an additional coating may bedisposed over extension 230 and any marker bands or wires positionedthereon to encase the assembly, as described in detail herein. An endview of flexible joint region 218 is shown in FIG. 9C, which illustratesthe variation of the push-pull wire lumen 214 formed adjacent to mainlumen 216. As shown, main lumen 216 may have a lubricious liner 244,such as polytetrafluoroethylene (PTFE), available commercially under thetrade name “TEFLON,” for example, defined upon an inner surface of mainlumen 216 to facilitate the insertion or removal of guidewires and/orother tools through the main lumen 216. Liner 244 may be formed from anyvariety of suitable polymeric materials, as described above.

The central and push-pull lumens of embodiments described herein arecircular (e.g., FIGS. 3, 9C, 9D, etc.). Upon activation of the push-pullwire into the push position, for example, the distal end deflects (e.g.,FIG. 4), causing the push-pull wire lumen to change shape from circularto oval. This ovalization results in a minor axis that is less thediameter of the circular push-pull wire lumen in the neutral orreference position and pinches (compresses) the push-pull wire. As thepush-pull wire is activated into the push position, the circular lumenbegins to ovalize and compress or pinch the push-pull wire, which canmake it relatively more difficult to deflect the catheter while thinningthe outer wall of the push-pull lumen.

More specifically, when the push-wire wire is activated from the neutralto the pull position (e.g., FIG. 4), the distal aspect of the catheterflexes or bends at the flexible joint region. The resultant flexion ofthe flexible joint in the pull position bends the catheter generallyabout a centroid of the cross section of the catheter, putting thepush-pull lumen in compression and shortening it relative to theopposite side of the catheter (which is in tension), causing the outerwall of the push-pull lumen to slightly pleat or have an undulatingsurface appearance at the bend.

Moreover, when the push-pull wire is activated from the neutral to thepush position (e.g., FIG. 4), the distal aspect of the catheter flexesor bends at the flexible joint region and in a direction opposite of thepull position. The flexion of the flexible joint in the push positionbends the catheter generally about a centroid of the cross section ofthe catheter, putting the push-pull lumen in tension and elongating itrelative to the opposite side of the catheter (which is in compression),causing the push-pull lumen to ovalize and pinching the push-pull wireand thinning the outer wall of the push-pull lumen.

From the aforementioned, the inherent effects on the cross-sectionalshape of the circular push-pull lumen when the push-pull wire isactuated are overcome in an embodiment by configuring the push-pulllumen to have an approximately oval cross-section instead of a circularcross-section. Alternatively, the inherent effects on thecross-sectional shape of the circular push-pull lumen when the push-pullwire is actuated are overcome in an embodiment by configuring thepush-pull wire as a flat wire instead of a circular wire. As such, aflat push-pull wire placed in an oval push-pull lumen is a relativelymore efficient design that increases the flexion of the flexible joint,reduces the push-pull force to actuate the push-pull wire, and preventsrupture of the outer wall of the push-pull lumen causing the push-pullwire to exit the ruptured wall.

Returning to FIG. 9B, tubing extension 230 may extend for a shortdistance past distal face 242, for instance, approximately 0.15 cm. Asshown in the side view of distal portion 250 in FIG. 10A, a radio-opaquemarker band 262, as described herein, may be attached over and/or ontoextension 230. The push-pull wire 258 positioned within wire lumen 214may extend through an opening in distal face 242 and attach to markerband 262. Push-pull wire 258 may be attached via a routing between band262 and extension 230 and bent around 260 marker band 262.Alternatively, additional marker bands may be positioned upon extension230 and used to sandwich the push-pull wire 258 between the respectivemarker bands. Other variations for attaching the wire 258 to the markerband 262 may also be used. The portion of extension 230 past marker band262 may be left or it may alternatively be trimmed flush against themarker band 262. An additional marker band may be positioned about thepush-pull wire lumen 214 to aid in positional orientation of thecatheter under an imaging system, such as a fluoroscope.

The flexible joint region 218 may flex beginning where braiding 236terminates 254. Flexible joint region 218 may also incorporate anoptional transitional joint region 252 between the flexible joint region218 and the remainder of the catheter body. This transition region 252may have an intermediate flexibility between that of joint region 218and the catheter body or it may be configured to be more flexible thaneither region to facilitate bending of the region. Flexibility may beimparted to region 252, at least in part, by omitting any liners orcoatings from the main lumen 216 and/or the wire lumen 214 along theregion 252. In either case, the transition region 252 may be omittedentirely. The covering or sheath 256, which is hydrophilic and may bedisposed over the entire device or portions of the device, may also beomitted from the flexible joint region 218. This covering 256 may alsobe included or omitted entirely from the transitional joint region 252,depending upon the desired results. Optionally, the distal portion ofthe device (optionally including the joint region 252), perhapsapproximately 35 to 50 cm, may be covered with the hydrophilic coating,again depending upon the desired results.

By varying the length of flexible joint region 218, the amount ofcurvature and flexure of the joint region 218 can be controlled. Forinstance, a joint region having a relatively shortened length betweenthe distal end of the joint region 218 and the terminal end 264 of thebraid, as shown in FIG. 10B, may allow for a reduced degree of flexure266 relative to a neutral position of the catheter. In comparison, asshown in FIG. 10C, a lengthened joint region extending to a moreproximally located terminal end 264′ may allow for a relatively greaterdegree of flexure 266′ relative to the flexure shown by the catheter inFIG. 10B. Accordingly, the degree of flexure may be controlled in partby the length of the flexible joint region. Thus, the flexible regionmay be flexed up to 90 degrees relative to the longitudinal axis of thecatheter assembly, and in some cases the flexible region may be flexedup to 180 degrees relative to the longitudinal axis depending upon thelength of the flexible joint region. To further facilitate bending ofthe catheter, additional members such as coils may be incorporated intothe device, for instance in the transitional region, to aid in furthercontrolling the bending of the joint region.

As mentioned above, the distal flexible joint region 218 may have acoating or liner 267, for example one that is hydrophilic for ease ofuse within a body, disposed over it and over extension 230 to encase theassembly, as shown in the cross-sectional side view of FIG. 11A. In thisvariation, marker band 262 may be disposed over the extension 230 and asecond marker band 269 may be disposed thereupon with the push-pull wire258 locked in between. In this variation, second marker band 269 islarger in diameter as well as length than marker band 262; however,other sizes and configurations may be used. The liner 267, which may befused down over the entire length of the joint region 218 or just aportion of the region 218, may be made of any variety of materialsdescribed herein. The marker bands 262, 269 may be utilized tofacilitate visualization of a position of the distal end of the device.Optionally, a third marker band 268 may be positioned along the deviceproximal to the joint region 218 to aid in visualizing potential coilingof the device.

In order to control the advancement or retraction of the push-pull wire,which controls the flexure of the flexible joint region, a variety ofcontrols may be utilized. FIGS. 12A to 12C show side, end, and partiallyremoved side views, respectively, of one variation of a control handle.A push-pull wire guide 270 may extend from handle 238 for transitioningthe push-pull wire to the catheter. As shown in the side view of FIG.12C, which shows handle 238 partially removed for clarity, wire control240 is configured as a wheel which further defines a concentricallyconfigured gear 272, as shown in FIG. 12D, which may engage with theengagement teeth 276 of rack 274, as shown in FIG. 12E. The push-pullwire may be attached to the rack 274 so that as control 240 is rotated,rack 274 may be advanced proximally or distally to thereby translate theattached push-pull wire along the longitudinal axis of the wire.

FIG. 13 shows another variation in the cross-sectional side view ofcombination fitting/handle assembly 280. Handle body 282 may incorporatethe push-pull handle portion 284 as an integrated part of a fitting. Theassembly 280 may include a main lumen access 286 as well as a push-pullwire access 288. FIG. 13 shows a cross-sectional side view of anothervariation in handle body 290. In this variation, a carriage screw 292may be positioned within the handle 290 such that a wire carriage 294 isconfigured to travel within advancement channel 296 defined withinhandle 290. A proximal end of carriage screw 292 may be attached to acontrol knob 298, which may be rotated to advance either proximally ordistally the carriage 294 and the push-pull wire, which may be attachedto carriage 294 at push-pull wire attachment 300.

In yet another variation in FIG. 15, handle body 310 may incorporate acontrol/release knob 312 which is attached to a release screw 314. Thescrew 314 may be attached to a wire carriage 316, which may attach topush-pull wire via attachment 318. As the knob 312 is translatedproximally or distally, carriage 316 may travel within channel 320 toeither advance or retract the attached push-pull wire. Knob 312 may betightened about screw 314 against handle 310 to lock a position of thepush-pull wire during flexure, if desired. In yet another variation inFIG. 16, handle body 330 may have a control slide 332 configured toproximally or distally advance a wire carriage 334 within handle 330.

FIGS. 17 and 18 illustrate another variation of a catheter assembly 340,having a catheter body 342 with a main lumen 346 defined through thelength of the catheter assembly. The push-pull wire lumen 344 may alsobe defined through the length of the catheter body, or at least througha majority of the length of catheter body, extending from a fitting (notshown) at a proximal end of the catheter assembly to a region near or atthe distal end of the device. The catheter body itself may compriseseveral regions, each having a different degree of flexibility. Bendingportion or flexible joint region 348 may be positioned at a distalsection 350 of the catheter assembly.

The push-pull wire lumen is reinforced along at least a substantialportion of its length, and, as described above, may include a braidedribbon 352 integrated throughout the length of push-pull wire lumenalong catheter body length, to terminate proximally of the flexiblejoint region. The push-pull wire lumen may have a liner 354, e.g., alubricious polymeric liner, disposed upon the lumen wall to facilitatemovement of the push-pull wire 356 in the lumen. The lubriciouspolymeric liner may be formed of a material with a low coefficient offriction, such as polytetrafluoroethylene (PTFE), for example, availablecommercially under the trade name “TEFLON,” although other similarmaterials with a low coefficient of friction, such as polyethylene orpolypropylene, for example, are also suitable, and the liner may be madefrom any variety of suitable polymeric materials such as are describedabove. The main lumen may also have such a lubricious liner 357. Thepush-pull wire is a tapered wire which has a larger diameter portion 358along a proximal portion and a smaller diameter distal portion 360 at ornear its distal end 362, and may be fabricated from a biocompatiblemetallic material such as stainless steel, platinum, and the like. Acoil 364 is placed around the smaller diameter portion, typicallyapproximately 6 cm at the end of an 8 cm long catheter, so that the tipof the push-pull wire does not deflect and rupture the otherwiseconstant diameter catheter. The coil has the effect of distributingstress along the smaller diameter portion of the push-pull wire toprevent buckling of the smaller diameter portion of the push-pull wire.The push-pull wire is also preferably coated with a material 366 with alow coefficient of friction, such as polytetrafluoroethylene, forexample, available commercially under the trade name “TEFLON,” althoughother similar materials with a low coefficient of friction, such aspolyethylene or polypropylene, for example, may also be suitable.

A radio-opaque marker band 368, as described above, may be attached overand/or onto the catheter body at or near the distal section of thecatheter assembly. The push-pull wire positioned within the push-pullwire lumen may attach to the marker band, such as by welding the distalend of the push-pull wire to a radially inner surface 370 of the markerband, for example, although the push-pull wire may be attached at itsdistal end to the catheter through a variety of methods, e.g.,adhesives, crimping, mechanical fasteners, and the like. An additionalmarker band may be positioned about the push-pull wire lumen to aid inpositional orientation of the catheter under an imaging system, such asa fluoroscope.

In another variation shown in FIG. 19, a strapping coil 372 may also beplaced around the outside of the catheter to prevent the catheter fromrupturing if the push-pull wire buckles when the push-pull wire ispushed. The strapping coil may be covered by an outer covering 374formed of a polymeric material, such as of PEBAX, for example, asdescribed herein. In another variation illustrated in FIGS. 20 and 21,an outer covering 376 of a very fine mesh formed of a polymericmaterial, such as polyethylene terephthalate (PET), for example, may beplaced over the distal tip of the catheter to prevent rupture of thelumen and reinforce the push-pull wire.

The applications of the catheter described herein are not limited tocertain treatments, but may include any number of vascular maladies.Modification of the above-described methods for carrying out theembodiments, and variations of the mechanical aspects of the embodimentsthat are obvious to those of skill in the mechanical and guide wireand/or catheter arts are intended to be within the scope of the claims.Moreover, various combinations of aspects between examples are alsocontemplated and are considered to be within the scope of thisdisclosure.

Embodiments described herein include a catheter or catheter section usedfor negotiating movement along small-diameter, tortuous vessels. Thecatheter may comprise a flexible joint region which defines a main lumenand an adjacent wire lumen, the wire lumen having an opening near or ata distal end of the flexible joint region; a push-pull wire configuredto be pushed or pulled along a longitudinal axis of the wire through thewire lumen; and wherein the flexible joint region has a predeterminedlength sized to affect a flexure of the flexible joint region. Moreover,the catheter assembly may further comprise at least one radio-opaquemarker band near or at the distal end of the flexible joint region forsecuring the push-pull wire thereto, wherein the flexible joint regionhas a predetermined length sized to affect a flexure of the flexiblejoint region.

An inflatable balloon member may optionally be used with the catheterassembly. If the inflatable member is utilized, the flexible joint mayvariously be distal of the inflatable member, within the inflatablemember, or proximal of the inflatable member.

One particular variation of the catheter assembly may have a catheterbody that defines a main lumen through the length of the assembly. Apush-pull wire lumen having an open distal end may also be definedthrough the length of the catheter body, or at least through a majorityof the length of catheter body, extending from a fitting at a proximalend of the catheter assembly to a region near or at the distal end ofthe device. The catheter body itself may be comprised of several regionseach having a different degree of flexibility. For instance, thecatheter assembly may comprise a first portion distal of the fittinghaving a first stiffness. A second portion, having a second stiffnessand located distal of the first portion, may be more flexible relativeto the first portion. Likewise, a third portion, having a thirdstiffness and located distal of the second portion, may be more flexiblerelative to the first and second portions. Thus, the catheter body mayhave a length comprised of progressively more flexible sections thefarther distally located along the catheter. Distal to the thirdsection, bending portion or flexible joint region may be positioned, asdescribed in detail herein.

The push-pull wire lumen may include a braided ribbon integratedthroughout the length of the lumen. Alternatively, the braided ribbonmay be integrated through the lumen to terminate proximally of the jointregion. The braided ribbon may be a uniform braid or it may be braidedwith a varying braid pitch. The braided ribbon may be made from a numberof materials. For example, metals that are members of a class of alloysknown as super-elastic alloys are used for the braid material of anembodiment, but are not so limited.

The manipulatable or flexible joint region is generally located at thedistal end of the catheter body and is configured to bend whenmanipulated by the push-pull wire. The bending portion itself may bevaried to extend to where the braid terminates, or it may be extended tothe bending portion to encompass a portion of the braid. By varying thelength of the flexible joint region, the amount of curvature and flexureof the joint region can be controlled. For instance, a joint regionhaving a relatively shortened length between the distal end of the jointregion and the terminal end of the braid may allow for a reduced degreeof flexure relative to a neutral position of the catheter. Incomparison, a lengthened joint region extending to a more proximallylocated terminal end may allow for a relatively greater degree offlexure. Accordingly, the degree of flexure may be controlled in part bythe length of the flexible joint region. Thus, the flexible region maybe flexed up to 90 degrees relative to the longitudinal axis of thecatheter assembly and in some cases, the flexible region may be flexedup to 180 degrees relative to the longitudinal axis depending upon thelength of the flexible joint region. To further facilitate bending ofthe catheter, additional members such as coils may be incorporated intothe device, for instance in the transitional region, to aid in furthercontrolling the bending of the joint region.

In another embodiment, the catheter section includes a tubing extensionextending distally from the main lumen of the distal end of the flexiblejoint region. In an embodiment, the radio-opaque marker band may beattached to the tubing extension. The push-pull wire typically extendsthrough the opening of the wire lumen at the distal end of the flexiblejoint region, and may be attached to the marker band attached to thetubing extension.

In another embodiment, the catheter section includes a control incommunication with a proximal end of the push-pull wire for manipulatingthe flexible joint region. The control typically includes a handlereceiving the proximal end of the push-pull wire; and a wire controlmember mounted to the handle and engaging the push-pull wire, wherebymovement of the wire control member translates the push-pull wire alongthe longitudinal axis of the push-pull wire. In one presently preferredaspect, the handle includes a push-pull wire guide extending from thehandle, and the push-pull wire passes through the push-pull wire guidefor transitioning the push-pull wire to the catheter body. In anotherpresently preferred aspect, the handle is integrated into a catheterfitting connected to the catheter body, the catheter fitting including amain lumen access and a push-pull wire access.

In another embodiment, the proximal end of the push-pull wire isattached to a rack bearing a plurality of engagement teeth, and the wirecontrol member engaging the engagement teeth of the rack, such thatmovement of the wire control member advances the rack proximally ordistally to thereby translate the attached push-pull wire along thelongitudinal axis of the push-pull wire. In an embodiment, the wirecontrol member includes a wheel defining a concentrically configuredgear engaging the engagement teeth of the rack, whereby rotation of thewheel advances the rack proximally or distally to thereby translate thepush-pull wire along the longitudinal axis of the push-pull wire.

In another embodiment, the proximal end of the push-pull wire isattached to a wire carriage, and the wire control member includes acarriage screw disposed within the handle, the wire carriage beingconfigured to travel within an advancement channel defined within thehandle, and a proximal end of the carriage screw being attached to acontrol knob that may be rotated to advance the wire carriage and thepush-pull wire either proximally or distally along the longitudinal axisof the push-pull wire.

In another embodiment, the proximal end of the push-pull wire isattached to a wire carriage, and the handle comprises a control releaseknob attached to a release screw attached to the wire carriage, wherebythe control release knob may be translated proximally or distally suchthat the wire carriage travels within an advancement channel to advanceor retract the push-pull wire. In an embodiment, the control releaseknob may be tightened about the release screw against the handle to locka position of the push-pull wire.

In another embodiment, the proximal end of the push-pull wire isattached to a wire carriage, and wherein the wire control membercomprises a control slide configured to proximally or distally advancethe wire carriage within the handle to thereby translate the push-pullwire along the longitudinal axis of the push-pull wire.

Another embodiment provides for a catheter section including a catheterbody having a proximal end and a distal end, the catheter body includinga distal flexible joint region, a main lumen extending through thecatheter body and through the flexible joint region, and a wire lumenadjacent to the main lumen and extending through the catheter body andthrough the flexible joint region. The wire lumen of the flexible jointregion has an opening near or at a distal end of the flexible jointregion, and a tapered push-pull wire is provided, having a proximalportion of a first diameter and a distal portion of a smaller diameterthan the first diameter. The push-pull wire is configured to be pushedor pulled along a longitudinal axis of the wire through the wire lumen,and the distal end of the push-pull wire is attached to the distalflexible joint region. In an embodiment, a coating of a material with alow coefficient of friction is disposed over the push-pull wire.

A coil is also disposed around the smaller diameter distal portion ofthe push-pull wire, which has the effect of distributing stress alongthe smaller diameter portion of the push-pull wire to prevent bucklingof the smaller diameter portion of the push-pull wire, so that the tipof the push-pull wire does not deflect and rupture the catheter body. Acontrol is also provided in communication with a proximal end of thepush-pull wire for manipulating the flexible joint region.

In another embodiment, a strapping coil is disposed around the outsideof the catheter, and an outer covering formed of a polymeric material,such as PEBAX, for example, may be disposed around the strapping coil.In another variation, an outer covering of a mesh formed of a polymericmaterial, such as polyethylene terephthalate, for example, may bedisposed around the distal tip of the catheter. In another embodiment,at least one radio-opaque band may be mounted to the catheter body nearor at the distal end of the flexible joint region, the push-pull wireextends through the opening of the wire lumen at the distal end of theflexible joint region, and push-pull wire is attached to the markerband. In another presently preferred aspect, the wire lumen furthercomprises a braid along at least a substantial portion of the wirelumen, and typically the braid terminates proximally of the flexiblejoint region. In another embodiment, the main lumen includes a lining,such as a lubricious lining, for example, along at least a substantialportion of the main lumen. The wire lumen may also be provided with alining, such as a lubricious lining, for example, along at least asubstantial portion of the wire lumen.

Embodiments described herein include a device comprising a cathetersection including a flexible joint region disposed between a distal endand a proximal end. The device includes a laser fiber disposed withinthe catheter section. The laser fiber emits laser light at a fiberdistal end. The device includes a wire comprising a distal end coupledto the catheter section. The wire is configured to move the distal endof the catheter section from a first position to a second position aboutthe flexible joint region.

Embodiments described herein include a device comprising: a cathetersection comprising a flexible joint region disposed between a distal endand a proximal end; a laser fiber disposed within the catheter section,wherein the laser fiber emits laser light at a fiber distal end; and awire comprising a distal end coupled to the catheter section, whereinthe wire is configured to move the distal end of the catheter sectionfrom a first position to a second position about the flexible jointregion.

The device of an embodiment comprises a first lumen disposed within thecatheter section, wherein the first lumen comprises an open distal endat the proximal end of the catheter section, wherein the wire isconfigured to be pushed and pulled through the first lumen along alongitudinal axis of the wire.

The device of an embodiment comprises a second lumen disposed within thecatheter section adjacent the first lumen, wherein the laser fiber isdeployed via the second lumen.

The device of an embodiment comprises a guidewire.

The guidewire of an embodiment is deployed via the second lumen.

The device of an embodiment comprises a guidewire lumen disposed withinthe catheter section adjacent the first lumen, wherein the guidewire isdeployed via the guidewire lumen.

The guidewire of an embodiment has at least one of a variable stiffnessalong its length and a stepped diameter along its length.

The device of an embodiment comprises a radio-opaque band fixed to thecatheter section.

The distal end of the wire of an embodiment is secured to theradio-opaque band.

The device of an embodiment comprises an inflatable member.

The flexible joint region of an embodiment is distal of the inflatablemember.

The flexible joint region of an embodiment is disposed within theinflatable member.

The flexible joint region of an embodiment is proximal of the inflatablemember.

The inflatable member of an embodiment comprises at least one ofelastomer, thermoplastic polymer, silicone rubber, latex rubber, naturalrubber, butadiene-based co-polymer, EPDM, polyvinyl chloride, complexco-polymer, styrene-ethylene butylene-styrene co-polymer, polyethylene,polypropylene, and Nylon.

The flexible joint region of an embodiment comprises a coil member.

The coil member of an embodiment includes a section comprising a pitchthat is larger than adjacent coil pitches.

The flexible joint region of an embodiment comprises a braid.

The braid of an embodiment comprises a section with a pic that is largerthan adjacent pics.

The flexible joint region of an embodiment comprises a polymer that isrelatively softer than at least one adjacent polymer.

The flexible joint region of an embodiment comprises a wall thicknessthat is relatively thinner than at least one adjacent wall thickness.

A method comprising forming a catheter section to include a flexiblejoint region disposed between a distal end and a proximal end. Themethod comprises housing a laser fiber within the catheter section. Thelaser fiber emits laser light at a fiber distal end. The methodcomprises housing a wire in the catheter section and coupling a distalend of the wire to the catheter section. The wire is configured to movethe distal end of the catheter section from a first position to a secondposition about the flexible joint region.

A method comprising: forming a catheter section to include a flexiblejoint region disposed between a distal end and a proximal end; housing alaser fiber within the catheter section, wherein the laser fiber emitslaser light at a fiber distal end; and housing a wire in the cathetersection and coupling a distal end of the wire to the catheter section,wherein the wire is configured to move the distal end of the cathetersection from a first position to a second position about the flexiblejoint region.

Embodiments described herein include a catheter section comprising acatheter body having a proximal end and a distal end. The catheter bodyincludes a distal flexible joint region, a main lumen extending throughthe catheter body and through the flexible joint region, and a wirelumen adjacent to the main lumen and extending through the catheter bodyand through the flexible joint region. The catheter body defines atleast a first region having a first flexibility and a second regionhaving a second flexibility more flexible than the first region. Thewire lumen of the flexible joint region has an opening near or at adistal end of the flexible joint region. The flexible joint region has apredetermined length sized to affect a flexure of the flexible jointregion. Embodiments include a push-pull wire configured to be pushed orpulled along a longitudinal axis of the wire through the wire lumen. Thedistal end of the push-pull wire is attached to the distal flexiblejoint region. Embodiments include a control in communication with aproximal end of the push-pull wire for manipulating the flexible jointregion.

Embodiments described herein include a catheter section comprising: acatheter body having a proximal end and a distal end, the catheter bodyincluding a distal flexible joint region, a main lumen extending throughthe catheter body and through the flexible joint region, and a wirelumen adjacent to the main lumen and extending through the catheter bodyand through the flexible joint region, the catheter body defining atleast a first region having a first flexibility and a second regionhaving a second flexibility more flexible than the first region, thewire lumen of the flexible joint region having an opening near or at adistal end of the flexible joint region, wherein the flexible jointregion has a predetermined length sized to affect a flexure of theflexible joint region; a push-pull wire configured to be pushed orpulled along a longitudinal axis of the wire through the wire lumen, thedistal end of the push-pull wire attached to the distal flexible jointregion; a control in communication with a proximal end of the push-pullwire for manipulating the flexible joint region.

The catheter section of an embodiment includes at least one radio-opaqueband near or at the distal end of the flexible joint region.

The first region of an embodiment is located distally of the secondregion.

The second region of an embodiment is located distally of the firstregion.

The catheter section of an embodiment includes a third region having athird flexibility more flexible than the second region.

The third region of an embodiment is located distally of the secondregion.

The wire lumen of an embodiment comprises a braid along at least asubstantial portion of the wire lumen.

The braid of an embodiment terminates proximally of the flexible jointregion.

The main lumen of an embodiment comprises a lining along at least asubstantial portion of the main lumen.

The lining of an embodiment comprises a lubricious lining.

The wire lumen of an embodiment comprises a lining along at least asubstantial portion of the wire lumen.

The lining of an embodiment comprises a lubricious lining.

The flexible joint region of an embodiment comprises a polymer which issofter than adjacent polymers.

The catheter section of an embodiment includes a coating over at least amajority of the flexible joint region.

The catheter section of an embodiment includes a tubing extensionextending distally from the main lumen of the distal end of the flexiblejoint region.

The catheter section of an embodiment includes a radio-opaque markerband attached to the tubing extension.

The push-pull wire of an embodiment through the opening of the wirelumen at the distal end of the flexible joint region, and is attached tothe marker band attached to the tubing extension.

The catheter section of an embodiment includes a radio-opaque markerband positioned about the push-pull wire lumen.

The control of an embodiment comprises: a handle receiving the proximalend of the push-pull wire; and a wire control member mounted to thehandle and engaging the push-pull wire, whereby movement of the wirecontrol member translates the push-pull wire along the longitudinal axisof the push-pull wire.

The handle of an embodiment comprises a push-pull wire guide extendingfrom the handle, and the push-pull wire passes through the push-pullwire guide for transitioning the push-pull wire to the catheter body.

The proximal end of the push-pull wire of an embodiment is attached to arack bearing a plurality of engagement teeth, and the wire controlmember engaging the engagement teeth of the rack, whereby movement ofthe wire control member advances the rack proximally or distally tothereby translate the attached push-pull wire along the longitudinalaxis of the push-pull wire.

The wire control member of an embodiment comprises a wheel defining aconcentrically configured gear engaging the engagement teeth of therack, whereby rotation of the wheel advances the rack proximally ordistally to thereby translate the push-pull wire along the longitudinalaxis of the push-pull wire.

The handle is integrated into a catheter fitting connected to thecatheter body, the catheter fitting including a main lumen access and apush-pull wire access.

The proximal end of the push-pull wire of an embodiment is attached to awire carriage, and the wire control member comprises a carriage screwdisposed within the handle, the wire carriage being configured to travelwithin an advancement channel defined within the handle, and a proximalend of the carriage screw being attached to a control knob that may berotated to advance the wire carriage and the push-pull wire eitherproximally or distally along the longitudinal axis of the push-pullwire.

The proximal end of the push-pull wire of an embodiment is attached to awire carriage, and the handle comprises a control release knob attachedto a release screw attached to the wire carriage, whereby the controlrelease knob may be translated proximally or distally such that the wirecarriage travels within an advancement channel to advance or retract thepush-pull wire.

The control release knob of an embodiment may be tightened about therelease screw against the handle to lock a position of the push-pullwire.

The proximal end of the push-pull wire of an embodiment is attached to awire carriage, and wherein the wire control member comprises a controlslide configured to proximally or distally advance the wire carriagewithin the handle to thereby translate the push-pull wire along thelongitudinal axis of the push-pull wire.

Embodiments described herein include a catheter section comprising acatheter body having a proximal end and a distal end. The catheter bodyincludes a distal flexible joint region, a main lumen extending throughthe catheter body and through the flexible joint region, and a wirelumen adjacent to the main lumen and extending through the catheter bodyand through the flexible joint region. The wire lumen of the flexiblejoint region has an opening near or at a distal end of the flexiblejoint region. Embodiments include a push-pull wire configured to bepushed or pulled along a longitudinal axis of the wire through the wirelumen. The distal end of the push-pull wire is attached to the distalflexible joint region. The push-pull wire has a proximal portion of afirst diameter and a distal portion of a smaller diameter than the firstdiameter. Embodiments include a coil disposed around the smallerdiameter distal portion of the push-pull wire. Embodiments include acontrol in communication with a proximal end of the push-pull wire formanipulating the flexible joint region.

Embodiments described herein include a catheter section comprising: acatheter body having a proximal end and a distal end, the catheter bodyincluding a distal flexible joint region, a main lumen extending throughthe catheter body and through the flexible joint region, and a wirelumen adjacent to the main lumen and extending through the catheter bodyand through the flexible joint region, the wire lumen of the flexiblejoint region having an opening near or at a distal end of the flexiblejoint region; a push-pull wire configured to be pushed or pulled along alongitudinal axis of the wire through the wire lumen, the distal end ofthe push-pull wire attached to the distal flexible joint region, thepush-pull wire having a proximal portion of a first diameter and adistal portion of a smaller diameter than the first diameter; a coildisposed around the smaller diameter distal portion of the push-pullwire; and a control in communication with a proximal end of thepush-pull wire for manipulating the flexible joint region.

The catheter section of an embodiment includes a coating of a materialwith a low coefficient of friction disposed over the push-pull wire.

The catheter section of an embodiment includes a strapping coil disposedaround the outside of the catheter.

The catheter section of an embodiment includes an outer covering formedof a polymeric material disposed around the strapping coil.

The outer covering disposed around the strapping coil of an embodimentis formed of PEBAX.

The catheter section of an embodiment includes an outer covering of amesh formed of a polymeric material disposed around the distal tip ofthe catheter.

The mesh of an embodiment is formed of polyethylene terephthalate.

The catheter section of an embodiment includes at least one radio-opaqueband near or at the distal end of the flexible joint region.

The wire lumen of an embodiment comprises a braid along at least asubstantial portion of the wire lumen.

The braid of an embodiment terminates proximally of the flexible jointregion.

The main lumen of an embodiment comprises a lining along at least asubstantial portion of the main lumen.

The lining of an embodiment comprises a lubricious lining.

The wire lumen of an embodiment comprises a lining along at least asubstantial portion of the wire lumen.

The lining of an embodiment comprises a lubricious lining.

The push-pull wire of an embodiment extends through the opening of thewire lumen at the distal end of the flexible joint region, and isattached to the marker band.

Unless the context clearly requires otherwise, throughout thedescription and the claims, the words “comprise,” “comprising,” and thelike are to be construed in an inclusive sense as opposed to anexclusive or exhaustive sense; that is to say, in a sense of “including,but not limited to.” Words using the singular or plural number alsoinclude the plural or singular number respectively. Additionally, thewords “herein,” “hereunder,” “above,” “below,” and words of similarimport, when used in this application, refer to this application as awhole and not to any particular portions of this application. When theword “or” is used in reference to a list of two or more items, that wordcovers all of the following interpretations of the word: any of theitems in the list, all of the items in the list and any combination ofthe items in the list.

The above description of embodiments of the device and correspondingsystems and methods is not intended to be exhaustive or to limit thesystems and methods to the precise forms disclosed. While specificembodiments of, and examples for, the device and corresponding systemsand methods are described herein for illustrative purposes, variousequivalent modifications are possible within the scope of the systemsand methods, as those skilled in the relevant art will recognize. Theteachings of the device and corresponding systems and methods providedherein can be applied to other systems and methods, not only for thesystems and methods described above.

The elements and acts of the various embodiments described above can becombined to provide further embodiments. These and other changes can bemade to the device and corresponding systems and methods in light of theabove detailed description.

In general, in the following claims, the terms used should not beconstrued to limit the device and corresponding systems and methods tothe specific embodiments disclosed in the specification and the claims,but should be construed to include all systems that operate under theclaims. Accordingly, the device and corresponding systems and methods isnot limited by the disclosure, but instead the scope is to be determinedentirely by the claims.

While certain aspects of the device and corresponding systems andmethods are presented below in certain claim forms, the inventorscontemplate the various aspects of the device and corresponding systemsand methods in any number of claim forms. Accordingly, the inventorsreserve the right to add additional claims after filing the applicationto pursue such additional claim forms for other aspects of the deviceand corresponding systems and methods.

What is claimed is:
 1. A device comprising: a catheter sectioncomprising a flexible joint region disposed between a distal end and aproximal end; a laser fiber disposed within the catheter section,wherein the laser fiber emits laser light at a fiber distal end; and awire comprising a distal end coupled to the catheter section, whereinthe wire is configured to move the distal end of the catheter sectionfrom a first position to a second position about the flexible jointregion.
 2. The device of claim 1, comprising a first lumen disposedwithin the catheter section, wherein the first lumen comprises an opendistal end at the proximal end of the catheter section, wherein the wireis configured to be pushed and pulled through the first lumen along alongitudinal axis of the wire.
 3. The device of claim 2, comprising asecond lumen disposed within the catheter section adjacent the firstlumen, wherein the laser fiber is deployed via the second lumen.
 4. Thedevice of claim 1, comprising a guidewire.
 5. The device of claim 4,wherein the guidewire is deployed via the second lumen.
 6. The device ofclaim 4, comprising a guidewire lumen disposed within the cathetersection adjacent the first lumen, wherein the guidewire is deployed viathe guidewire lumen.
 7. The device of claim 4, wherein the guidewire hasat least one of a variable stiffness along its length and a steppeddiameter along its length.
 8. The device of claim 1, comprising aradio-opaque band fixed to the catheter section.
 9. The device of claim8, wherein the distal end of the wire is secured to the radio-opaqueband.
 10. The device of claim 1, comprising an inflatable member. 11.The device of claim 10, wherein the flexible joint region is distal ofthe inflatable member.
 12. The device of claim 10, wherein the flexiblejoint region is disposed within the inflatable member.
 13. The device ofclaim 10, wherein the flexible joint region is proximal of theinflatable member.
 14. The device of claim 10, wherein the inflatablemember comprises at least one of elastomer, thermoplastic polymer,silicone rubber, latex rubber, natural rubber, butadiene-basedco-polymer, EPDM, polyvinyl chloride, complex co-polymer,styrene-ethylene butylene-styrene co-polymer, polyethylene,polypropylene, and Nylon.
 15. The device of claim 1, wherein theflexible joint region comprises a coil member.
 16. The device of claim15, wherein the coil member includes a section comprising a pitch thatis larger than adjacent coil pitches.
 17. The device of claim 1, whereinthe flexible joint region comprises a braid.
 18. The device of claim 17,wherein the braid comprises a section with a pic that is larger thanadjacent pics.
 19. The device of claim 1, wherein the flexible jointregion comprises a polymer that is relatively softer than at least oneadjacent polymer.
 20. The device of claim 1, wherein the flexible jointregion comprises a wall thickness that is relatively thinner than atleast one adjacent wall thickness.
 21. A method comprising: forming acatheter section to include a flexible joint region disposed between adistal end and a proximal end; housing a laser fiber within the cathetersection, wherein the laser fiber emits laser light at a fiber distalend; and housing a wire in the catheter section and coupling a distalend of the wire to the catheter section, wherein the wire is configuredto move the distal end of the catheter section from a first position toa second position about the flexible joint region.